CN105658273B - The Target Assignment of the implant electrode band based on excitation extension - Google Patents
The Target Assignment of the implant electrode band based on excitation extension Download PDFInfo
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- CN105658273B CN105658273B CN201480057261.5A CN201480057261A CN105658273B CN 105658273 B CN105658273 B CN 105658273B CN 201480057261 A CN201480057261 A CN 201480057261A CN 105658273 B CN105658273 B CN 105658273B
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/0526—Head electrodes
- A61N1/0541—Cochlear electrodes
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/08—Arrangements or circuits for monitoring, protecting, controlling or indicating
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
- A61N1/36038—Cochlear stimulation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
- A61N1/36038—Cochlear stimulation
- A61N1/36039—Cochlear stimulation fitting procedures
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/08—Arrangements or circuits for monitoring, protecting, controlling or indicating
- A61N2001/083—Monitoring integrity of contacts, e.g. by impedance measurement
Abstract
Describe a kind of cochlea implantation device for producing sound perception in the patient of implantation.Implant electrode include electrode wires, for corresponding electrode contact transmit stimulus signal, the electrode contact along the top electrode array part of implant electrode outer surface distribution of lengths.It is characterised by the top of electrod-array, when the cochlea of patient is inserted, trend has opposite folding with the more bottom of array electrode.Implantable stimulation process device produces stimulus signal, stimulus signal is transmitted with certain frequency band to include each electrode contact of any opposing sheets part, the function of spatial spread of the frequency band based on stimulation voltage is limited, and is correctly associated with the tonequality frequency response of neighboring neurological tissue.
Description
The priority of the U.S. Provisional Patent Application 61/891,930 submitted to this application claims on October 17th, 2013, its is complete
Portion's content is quoted comprising herein.
Technical field
Coding boost pulse the present invention relates to be used for cochlea implantation system.
Background technology
Normal ear transmission sound is as shown in figure 1, by external ear 101 to eardrum (ear-drum) 102, it moves middle ear 103
Bone (malleus, incus and stapes), these bones vibration cochlea 104 oval window and ox-eye opening.Cochlea 104 is
Long, narrow pipe, twist winds about two half-turns along its axle.It includes being referred to as the upper channel of vestibular canal, and is referred to as
The lower channel of tympanic canal, both are connected by cochlear duct.Cochlea 104 forms vertical spin cone, and its center is referred to as modiolus, auditory nerve
113 SGC is resided at herein.The sound that response is transmitted and received by middle ear 103, hydraulically full cochlea 104
As transducer, produce electric pulse to be sent to cochlea nerve 113, be ultimately delivered to brain.
Asked when being converted to exist along the ability of the significant action potential of the neural matrix of cochlea 104 external voice
During topic, impaired hearing.In order to improve impaired hearing, auditory prosthesis have been developed.For example, being related to middle ear 103 when damaging
During operation, conventional audiphone can be used to provide the sound mechanical stimulus that sound amplifies form to auditory system.Or, work as damage
When being associated with cochlea 104, the cochlear implantation prosthesis with implant electrode contact can be connect with by the multi-electrode along distribution of electrodes
Touch the low current electro photoluminescence auditory nerve tissue of transmission.
Fig. 1 also illustrates some elements of typical cochlea implantation system, including offer voice signal is input at external signal
The external microphone of device 111 is managed, processor 111 can implement various signal transacting schemes.Then the signal through processing is converted to
The sequence of digital data format, such as data frame, for sending implant 108. to by coil 107.Except receiving at
The acoustic information of reason, implant 108 also performs other signal transacting, such as error correction, pulse shaping etc., and produces thorn
Energizing mode (based on the acoustic information for extracting), the electrod-array 110 of implantation is sent to by electrode cable 109.
Along the extending shaft of electrod-array 110, on its surface there are multiple electrodes to contact 112, it provides cochlea 104
Stimulation, such as single-phase stimulation or overlap biphasic impulse may be selected.Spacing between electrode contact 112 can be fixed or variable
's.For example, the electrode contact 112 in the bottom of electrod-array 110 (enters the place of cochlea closer to array, such as by ellipse
Circular window) there may be broader spacing than those electrode contacts on the top of electrod-array 110.
Many existing cochlea implantation stimulus coding strategies represent that the mode of voice signal is to be separated into not voice signal
With frequency band, and extract these frequency bands envelopes (i.e. energy) of each.The envelope of these voice signals is represented for limiting
It is applied to the impulse amplitude of the boost pulse of each electrode.The number of bandpass signal is typically equal to the number of stimulating electrode, needs
Relatively wide frequency band is wanted to cover audio frequency range.Each electrode contact is to its neighbouring nerve fiber transmission reaction cochlea
The electrical stimulation signal of the restriction frequency band of tonequality tissue.
Due to determining that place spacing is quite time-consuming using psychologic acoustics flow, of cochlea implantation (CI) assembling is ignored
Aspect be each electrode channel bandwidth assignment optimization.Generally, the spacing of perception and the neural activation along cochlea (tonequality)
Position strong correlation.In normal good hearing, frequency-position mapping is logarithmic relationship, by Greenwood (Greenwood, 1961)
Limit.When several electrode channels encourage the similar area of neuronal structure, can expect more or less to be equal to the spacing for perceiving.
If these electrode channels represent the different frequency bands signal for being applied to identical neurons, obscuring for room and time can be caused.
During electrode implant surgery, electrod-array is advanced to surgeon the bottom of cochlea tympanic canal by oval window
End, so that the end of electrod-array reaches cochlea apex zone.But the high resiliency of electrod-array means that surgery inserts flow
Carry electrod-array in cochlea " folding " greater risk.Particularly, the top of electrod-array may fold, and fold top
Interior electrode contact will not arrive at the apex zone of cochlea, but will stimulate the more bottom zone of cochlea, and this will cause is planted
Enter patient's spacing and obscure hearing impression.
Such electrode is folded and can detected by imaging method, for example computed tomography (Grolman etc.,
“Spread of Excitation Measurements for the Detection of Electrode Array
Foldovers:A Prospective Study Comparing 3-Dimensional Rotational X-ray and
Intraoperative Spread of Excitation Measurements”,2008).Such complicated and expensive flow
It is required, because other measurements, such as eCAP does not allow the nonreactive region of neuron nerve and electrode to fold what is occurred
Differentiation between region；The measurement result does not allow to set up any standard comes area in two kinds of situation.
The content of the invention
Embodiments of the invention are used to detect the cochlear implant electrode folding position of implantation.It is every for implant electrode array
Individual electrode contact, performs eCAP measurements.Then to each electrode contact, as the function that eCAP is measured, calculating current extension.Base
In the calculating of current expansion, it is determined that the top of electrod-array folding position, wherein electrod-array and the more bottom of electrod-array
Opposing sheets.
In further specific embodiment, neural activation spatial spread voltage can be performed to each electrode contact and surveyed
Amount, then as eCAP measurements and the function of spatial spread voltage measurement, calculating current extension.Or, can be to each electrode
Contact performs impedance remote measurement (IFT) measurement, and the function calculating current for then being measured as eCAP measurements and IFT extends.To every
Individual electrode contact calculating current extension can be used on the electrode contact of restricted number of the measured electrode contact per side.
Embodiments of the invention also include new cochlea implantation device, for producing sound perception in implantation patient.Plant
Enter electrode and include the electrode wires for stimulus signal to be sent to corresponding electrode contact, these electrode contacts are along implant electrode
The distribution of lengths of the outer surface of top electrode array portion.It is characterised by working as at the top of electrod-array and is inserted into the cochlea of patient
When, the part for electrod-array more bottom is easy to opposing sheets.Implantable stimulation process device produces stimulus signal, to wrap
Include each electrode contact of any opposing sheets part and thorn is transmitted with the frequency band that the spatial spread function based on stimulation voltage is limited
Energizing signal, and be correctly associated with the tonequality frequency response of neighboring neurological tissue.
The function of space current extension can be based further on amplitude Growth Function and/or exponential function.Space current extends
Function can be based on impedance remote measurement (IFT) measurement.Space current spread function can be limited using spatial spreading.
Brief description of the drawings
Fig. 1 represents the anatomical structure of the human ear with cochlea implantation system.
Fig. 2 represents that preferable eCAP Growth Functions are the curve maps of the function of stimulating current.
Fig. 3 is represented from one group of curve map of the spatial spread voltage of experiment.
Fig. 4 represents the curve map that current expansion when folding is simulated between electrode contact 3 and 4.
Fig. 5 represents the curve map of the spatial spread voltage of the current expansion from Fig. 4.
Fig. 6 represents the curve map of the estimation current expansion determined by the spatial spread of Fig. 5.
Fig. 7 represents the curve map with difference between current between the adjacent electrode for folding between electrode contact 3 and 4.
Fig. 8 represents the curve map of the electrode contact frequency distribution based on Greenwood functions.
Fig. 9 diagrams are inserted into the concept of the electrode contact angle of the electrod-array in patient cochlea.
Figure 10 representation spaces extend the example of function of voltage superposition of data.
Specific embodiment
The current expansion that embodiments of the invention relate to the use of electrode contact comes folding and the stimulation period of detecting electrode array
Between subsequent adaptation.Once detecting folding, mapping of the electrode contact to various frequency channels can be made, be reflected according to this
Penetrate the optimal bandwidth assignment for drawing each electrode contact.Calculating current can extend in a variety of ways, such as by neural activation
Spatial spread (SS) voltage measurement and eCAP (electrically-evoked compound action potential) threshold measurements or by impedance remote measurement (IFT).
Since one specific embodiment determine amplitude Growth Function and eCAP threshold values, detecting electrode array folding performing eCAP and measuring
It is folded.In space current extension SS measurements, constant stimulation electric current is used to each electrode contact.This allows the SS electricity based on measurement
The current expansion of pressure is estimated, wherein can be used interpolation method to obtain complete data any value (detectable without eCAP) for lacking
Collection.
The electrode contact j of the electrod-array with N number of electrode contact, since the top electrode contact 1 of electrod-array,
Bottommost electrode contact N to electrod-array is numbered.ECAP voltages are by measuring the eCAP response signals between N1 and P1
Peak-to-peak voltage difference and obtain (Seyle, k.and Brown, C.J., " Speech perception using maps based
on neural response telemetry measures",Ear Hear 23(1Suppl.),pages 72S-79S,
2002).It is appreciated that other eCAP response peak-to-peak signals can be used in identical mode, such as N1 and P2, or their knot
Close.It is approximate for first, when specific threshold value eCAPthr intersects, typical peak-to-peak eCAP voltages UP1-N1With stimulating current I lines
Property related (Growth Function).Under the stimulating current, there is no measurable eCAP to respond, UP1-N1=0.Ideal linearity Growth Function
It is described as shown in Figure 2：
UP1-N1=max (d × (I-eCAPthr), 0) (formula 1)
In the measurement shown in Fig. 2, eCAPthr is 300 μ A, slope d=0.8V/ μ A.Slope d and threshold value eCAPthr according to
Rely in neuronal survival and geometrical property, such as the distance between position, neuron and electrode contact, and from electrode contact to electricity
Pole contacts and respective change.Alternatively, in addition to linear amplitude increases, other models can similarly work, for example index
Model：
UP1-N1=f (I, eCAPthr)
In the SS voltage curves for crossing electrode contact, from stimulating electrode contact start, it is contemplated that on straight cochlea
Monotonically decreasing function, the best orientation with electrod-array assumes that the neuronal survival of homogeneity (does not have " dead " without folding
Area).This can find out in the curve e6h and e7h of Fig. 3.In low neuronal survival area (shadow region), such as curve e6i of Fig. 3 and
Shown in e7i, neural response reduces, and causes the sinking of SS voltage curves or value reduction.The appearance that electrode is folded, except SS curves
In stimulating electrode outside, by sink or other peak represent (Grolman etc., 2008).Such sinking can by dead band and
Fold both situation to represent, not any other information (such as radioscopic image or CT scan), this can not possibly be distinguished
Two kinds of different situations.
In order to overcome this problem, because current expansion is not influenceed by neuronal survival relatively, corresponding current expansion can
SS voltages and eCAPthr based on measurement are calculated.Therefore, to each electrode contact i and SS matrixes SSi,j, eCAP threshold values
eCAPthriCan be determined, row coefficient i represents that stimulating electrode is contacted, and row coefficient j represents the electrode contact of measurement.Stimulating current
I0It is determined, so as to whole array contact i, max (eCAPthr to electrod-arrayi) ＜ I0≤min(MCLi).In order to complete
eCAPthriAnd SSi,jData set, the value of any omission may be by spline function or any other suitable object function
Obtained by interpolation.Spatial spread voltage matrix SSi,jWith current expansion matrix Ii,jRelation give normalization SS matrixes
SSnormi,j：
Assuming that to each electrode contact, equal stimulating current I0It is acceptable simplification, it does not rely on the width for providing
Degree Growth Function.Generally, to each electrode contact, different specific stimulating current I is used0iInstead of common electric current I0Being can
Can.As the MCL on electrod-arrayiAnd eCAPthriElectric current does not allow to use common electric current I as described above0When, this is special
It is unimportant.In this case, SSnorm is calculated using identical formula 2i,j, but electricity is specifically stimulated with electrode contact
Stream I0iSubstitute the stimulating current I general to whole electrode contact i0。
Stimulating current I0, or in electrode contact particular stimulation electric current I0iIn the case of, an electrode contact is applied to,
Voltage U is measured on other electrode contactsP1-N1.This measurement can be repeated several times, can be with estimated voltage from these measurements
UP1-N1.The measurement is further repeated to each electrode contact i of electrod-array.
Due to not being obtained in that stimulating electrode contacts the measurement of i, using the stimulating current I for applying0Or connect in electrode
Touch particular stimulation electric current I0iIn the case of, SS is calculated by the model of amplitude Growth Functioni,j.In amplitude Growth Function model
Any proportionality coefficient is offset.In linear model, this is slope dj。
The current expansion I of the electrode contact j with stimulating electrode contact i and measurementi,jCan be calculated by measuring SS voltages
Come, it is contemplated that amplitude Growth Function, it is as follows：
Difference Di,kSo calculate, if k<I, then Ii,k+1-Ii,kIf, k >=i, Ii,k-Ii,k+1.Here, i tables
Show the electrode contact being stimulated, k is the coefficient from 1 to N-1, and wherein N is the number that electrod-array has electrode contact.Note,
This is more than a derivative.
Also can be measured by impedance remote measurement (IFT) and estimate current expansion Ii,j.In this case, in float electrode and
Stimulation artifact on public ground electrode is needed in measurement voltage matrix Ui,jWhen consider.Hindered based on the voltage matrix and passage
Anti- Zj, current expansion matrix can calculate by following formula
In figures 4 and 5, show when electrode contact 1,3,5 or 7 is stimulated at 800 μ A and electrode is folded and is located at electricity
Pole contacts I when between 3 and 4i,jAnd SSi,jData set.This is by position vector x=[6.5 5.5 4.5 456789 10
11 12] and threshold value eCAPthr=300e-6* [0.97 0.80 0.90 0.77 0.71 1.00 0.72 0.97 0.82
0.71 0.92 0.96] simulate.In Figure 5, the SS of electrode contact 77,jExtension, for example, have some in electrode contact 4,7,10
Individual turning point.Based on formula 3, as shown in fig. 6, when only one turning point is in ecs 7 at electrode contact 4, below
Current expansion I7,jCan be estimated.This causes the easy detection that electrode is folded, wherein for (stimulating electricity except global maximum
Pole contact i position) outside local maximum use and scan estimate Ii,jElectric current, because other local maximum can
Represent and fold.
In order to avoid turning to crosstalk, only the electrode contact of restricted number is contemplated that for assessing, that is, be not more than away from thorn
Swash some given number adjacent electrodes contact of electrode contact.The electrode contact of the number is referred to as window size, and symmetrically
Extend in the both sides of stimulating electrode contact.This can reflect electrode contact angle of departure α as shown in Figure 9, be characterised by that electrode connects
Touch the angular separation between 902 (on the angular vertex on center cochlear axis 901).Specific patient's physiology is relied on, it is different
Contact separation angle α can be adapted to, including location-dependent query angle.For example, top electrode contact can be by larger angular separation, more
The electrode contact of bottom can be by less angular separation.The function of the angle that any mapping relies on electrode contact locations can also be fitted
With.Typically, between electrode contact 902 contact separation angle α is average at 55 ° or so.In order to avoid turn to crosstalk, the leftmost side and
Maximum angle between rightmost side electrode contact 902, can for example be limited in no more than 270 °.Electrode contact spacing typically exists
The electrod-array of 2mm or so, it may be determined that window size is 9.Connect according to the electrod-array, the leftmost side and the rightmost side electrode that use
The size of Maximum Contact angle of departure α and cochlea between 902 is touched, actual specific window size can change, adjacent to determine
Contact separation angle α between electrode contact 902, and changed according to the difference of patient and patient.
Fig. 7 represents the difference between adjacent electrode contact, wherein for example, curve d1 is represented when electrode contact 1 is stimulated
Data.So, d1 curves correspond to the D of any k for being adapted to window size1,k.For any k, d1 outside window size
Line will be cut off and be arranged to zero.Once d1 functions are exported, the detection of folding is advanced to more from bottommost motor contact start
Tip contact, finds and represents that electrode folds the first zero crossing for occurring.If there is no such zero crossing, then just do not go out
Now fold.In the figure 7, curve d5 has zero crossing between electrode contact 3 and 4, and expression occurs in that electrode is folded therebetween.
Based on testing result is folded, new electrode contact to the distribution of frequency band can be performed.It is interested for bandwidth assignment
Be the sensation of electro photoluminescence, therefore normalization spatial spread voltage matrix SSnorm is used belowi,j。
In a detailed embodiment, it is represented by electrod-array along the spatial spread of the electrode contact dimension j of measurement
The function of Top electrode contact position, by spatial spread voltage matrix SSi,jBe converted to one group of function SSi(x), wherein i is to stimulate electricity
Pole contacts, and x is the position on electrod-array in the one-dimensional space.Function SSi(x)Can be normalized, window size is converted to electrode
Length on array.As shown in Figure 10, from labeled as xiStimulating electrode contact i position start, be limited to spatial spread voltage
Function PaiTop-direction determined by electrode position x, wherein function SSi(x)Reach or be reduced to particular bound SSlimitWith
Under, or the position for reaching window size.In an identical manner, bottom direction limitation is designated Pbi.Bottom direction and top side
Can be with difference, and responsible position and/or electrode contact i to limitation.The limitation can be from the measurement of the spatial spread of measurement
SSi,jStatistical property and/or desired wave filter group characteristic obtain.
In another specific example, contacted for each stimulating electrode along measuring electrode contact dimension j, normalization is empty
Between extend voltage matrix SSnormi,jIt is sampled.It means that i is contacted for stimulating electrode, it is any between electrode contact j
Measured value can be interpolated.Any suitable interpolation, such as linear or batten can be used.These interpolation or up-sampling value
SSint can be labeled asi,f, wherein f is up-sampling coefficient, and M point is introduced between adjacent electrode contact：
F=1,1+1/M, 1+2/M ... and 1+ (M-1)/M, 2 ..., N }.In one example, up-sampling is represented by：
PaiAnd PbiValue determine in the same manner as described above, but, for example limitation can be represented in the form of dB, for example-
3dB.Note, if SSjj=max (SSij) (this may not be always true), then SSnorm has been normalized, therefore SSint is
Through including normalization and by max (SSinti,f) remove, it should correspond to SSi,i*MAnd it has been 1, wherein M is up-sampling parameter.
Be can be thus completed according to the normalization (Byrne etc., 1994) that long-term average speech is composed：In the range of the limitation of upper and lower group of frequencies
(such as according to Greenwood frequencies-ground point function), the maximum relative to spectrum additionally increases long-term dB values, or for a long time
Average speech spectrum can also be used in spatial spreading limitation SSlimit.
Whole electrode contact N to electrod-array have determined that PaiAnd Pbi, next step is to determine overlap coefficient
Oindexi, the wherein coefficient represents the percentage overlapped between adjacent electrode contact, according to spatial spread (passage interaction)：
Referring to Figure 10.Then electrode contact i with limitation OlimitCompare, these OindexiIt is equal to or over OlimitElectricity
Pole contact is excluded.For whole electrode contacts, OlimitCan be fixed value, or it can be specific electrode contact, example
Such as, as the function of electrod-array Top electrode contact position x.
Then in the case where an electrode contact is excluded, electrode contact is given coefficient again.This can be so complete
Into：For example, comparing the electrode contact i and O since bottommost electrode contactlimit(its position for considering electrode contact), or
It is determined that being completed after the electrode contact to be all excluded.The electrode contact coefficient that these are reassigned represents by following e,
Do not include new coefficient, namely e=i.For example, OlimitCan be defined as：
Wherein median (Oindexi) be electrod-array whole electrode contact N intermediate value, OoffsetAnd OpropIt is single
Constant (for example, being equal to zero).In OlimitIn the case of being negative value, folding is detected and remapped can be as described herein
Perform.
Then relatively low Pl is calculated to the electrode contact e that retains on an arrayePh highereOff-position.Example
Such as, this includes calculating：
With
The position of electrode contact e is by PeRepresent.For electrode e=1 and e=N, symmetric bandwidth is calculated.The first electricity is not used
Symmetric bandwidth in pole and final electrode, average bandwidth can be calculated as：
With
Finally, with the help of the Greenwood functions as mapping function, can be with to the frequency band of each electrode contact e
According to relatively low PlePh highereOff-position is calculated：
F=A × (10αx- k) (formula 10)
A, α and k constant are selected based on sex or other physiology empirical values.For example, for adult male, representative value can
Being A=165.4, α=2.1, k=0.88.Selectivity constant α represents the ratio of base length so as to x.Or mapping can be by public affairs
The empirical value estimation known.By position Pa on electrod-array1The low-limit frequency of bottommost electrode contact covering is typically F1=
100Hz, by position Pb on electrod-arrayNThe highest frequency of top electrode contact covering is typically F2=8500Hz.By two
Frequency inserts Greenwood functions, can calculate x1And x2, x1Correspondence is on cochlea frequency top position, x2Correspondence on
Cochlea frequency lowest position.Thus, the position on electrod-array may map to frequency field f in cochlea：
F=A × (10αx- k), and
One group of result of experiment is as shown in figure 8, which use frequency limit F above1And F2, it is assumed that with width
Pbe-PaeSymmetric extension around=1 electrode contact e.Intersection in Greenwood functions and with limit, shows frequency band
Limitation.
Embodiments of the invention can be realized partly with traditional computer programming language.For example, it is preferable to embodiment can be with
Realized with the programming language (such as " C++ ", Python) of flow programming language (such as " C ") or object-oriented.The present invention can
The embodiment of replacement can realize being the combination of preprogrammed hardware elements, other associated components or hardware and software component.
Embodiment can be implemented partly as with computer program product in computer systems.These realizations may include one
Series is fixed on tangible medium, such as computer on computer-readable medium (such as disk, CD-ROM, ROM or hard disk)
Instruction, or the computer instruction of computer system is sent to by modem or other interface equipments, for example it is being situated between
The communication adapter of network is connected in matter.The medium can be tangible medium (such as optics or analog communications lines) or logical
Cross the medium of wireless technology (such as microwave, infrared or other transmission technologys) realization.The series of computer instructions all or
Partly embody the function on system described previously herein.It will be appreciated by those skilled in the art that such computer instruction
The multiple programs language for many Computer Architectures or operating system can be written as.And, such instruction is storable in
In any memory devices, such as semiconductor, magnetic, light or other memory devices, and transmitted using any communication technology, example
Such as optics, infrared, microwave or other tranmission techniques.Expect such computer program product be distributed as have with printing or
The removable medium (such as compressed package software) of person's electronic document, preloads computer system (for example, in system ROM or fixation
On disk), or realized from server or BBS on network (such as internet or WWW).Certainly, originally
Some embodiments of invention can realize the combination for software (such as computer program product) and hardware.Other reality of the invention
Apply example and be embodied as whole hardware, or whole softwares (such as computer program product).
Although it is disclosed that various example embodiments of the invention, without departing from the present invention, ability
Field technique personnel obviously can be so that various changes can be made and modification, and this will also obtain some advantages of the invention.
Claims (4)
1. a kind of cochlear implant electrode measurement apparatus, including：
The device of eCAP measurements is performed to each electrode contact in the electrod-array of implantation；
To each electrode contact, as the function that eCAP is measured, the device of calculating current extension；And
Calculated based on current expansion, determine the device of position folded in electrod-array, wherein the top of electrod-array have with
The opposite folding in the more bottom of electrod-array.
2. measurement apparatus according to claim 1, further include：
The device of neural activation spatial spread voltage measurement is performed to each electrode contact, and wherein calculating current is expanded to
ECAP measures the function with spatial spread voltage measurement.
3. measurement apparatus according to claim 1, further include：
The device of impedance remote measurement measurement is performed to each electrode contact, and wherein calculating current expands to eCAP measurements and hinders
The function of anti-field remote measurement measurement.
4. measurement apparatus according to claim 1, wherein using the device of each electrode contact calculating current extension
The electrode contact of the restricted number on the every side of the electrode contact of measurement.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US201361891930P | 2013-10-17 | 2013-10-17 | |
| US61/891,930 | 2013-10-17 | ||
| PCT/US2014/061032 WO2015058030A1 (en) | 2013-10-17 | 2014-10-17 | Objective allocation of implant electrode bands based on excitation spread |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN105658273A CN105658273A (en) | 2016-06-08 |
| CN105658273B true CN105658273B (en) | 2017-06-30 |
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| CN201480057261.5A Active CN105658273B (en) | 2013-10-17 | 2014-10-17 | The Target Assignment of the implant electrode band based on excitation extension |
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|---|---|
| US (1) | US9320887B2 (en) |
| EP (1) | EP3057653A4 (en) |
| CN (1) | CN105658273B (en) |
| AU (2) | AU2014337207B2 (en) |
| WO (1) | WO2015058030A1 (en) |
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|---|---|---|---|---|
| WO2017075219A1 (en) * | 2015-10-27 | 2017-05-04 | Vanderbilt University | Current steering compatible image-guided cochlear implant electrode deactivation methods and applications of same |
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| AU2014337207B2 (en) | 2017-03-02 |
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| AU2017200752A1 (en) | 2017-03-02 |
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